US7596253B2 - Method and apparatus for detection of caries - Google Patents

Method and apparatus for detection of caries Download PDF

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US7596253B2
US7596253B2 US11/262,869 US26286905A US7596253B2 US 7596253 B2 US7596253 B2 US 7596253B2 US 26286905 A US26286905 A US 26286905A US 7596253 B2 US7596253 B2 US 7596253B2
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tooth
image data
image
fluorescence
incident light
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US20070099148A1 (en
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Victor C. Wong
Rongguang Liang
Donna K. Rankin-Parobek
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Carestream Dental LLC
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Carestream Health Inc
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Priority to US11/262,869 priority Critical patent/US7596253B2/en
Priority to PCT/US2006/040472 priority patent/WO2007053293A2/en
Priority to JP2008537765A priority patent/JP5441411B2/ja
Priority to EP06826069A priority patent/EP1942794A2/en
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Priority to US13/117,724 priority patent/US8345942B2/en
Priority to US13/117,759 priority patent/US8396272B2/en
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Priority to US13/686,081 priority patent/US9247241B2/en
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    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
    • H04N17/00—Diagnosis, testing or measuring for television systems or their details
    • H04N17/002—Diagnosis, testing or measuring for television systems or their details for television cameras
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
    • A61B5/0088—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for oral or dental tissue

Definitions

  • This invention generally relates to a method and apparatus for dental imaging and more particularly to an improved method for early detection of caries using fluorescence and scattering of light.
  • QLF quantitative light-induced fluorescence
  • U.S. Patent Application Publication No. 2004/0202356 (Stookey et al.) describes mathematical processing of spectral changes in fluorescence in order to detect caries in different stages with improved accuracy. Acknowledging the difficulty of early detection when using spectral fluorescence measurements, the '2356 Stookey et al. disclosure describes approaches for enhancing the spectral values obtained, effecting a transformation of the spectral data that is adapted to the spectral response of the camera that obtains the fluorescent image.
  • the present invention provides a method for obtaining an image of tooth tissue using a processing apparatus or computer with a display to perform steps comprising:
  • the enhanced image may be printed.
  • a feature of the present invention is that it utilizes both fluorescence and reflectance image data for dental imaging.
  • An advantage of the present invention is that it offers enhancement over existing fluorescence imaging techniques and is useful for detection of caries in its incipient stages.
  • FIG. 1 is a schematic block diagram of an imaging apparatus for caries detection according to one embodiment
  • FIG. 2 is a schematic block diagram of an imaging apparatus for caries detection according to an alternate embodiment
  • FIG. 3 is a schematic block diagram of an imaging apparatus for caries detection according to an alternate embodiment
  • FIG. 4A is a schematic block diagram of an imaging apparatus for caries detection according to an alternate embodiment using polarized light
  • FIG. 4B is a schematic block diagram of an imaging apparatus for caries detection according to an alternate embodiment using a polarizing beamsplitter to provide polarized light and to minimize specular reflection;
  • FIG. 5 is a view showing the process for combining dental image data to generate a fluorescence image with reflectance enhancement according to the present invention
  • FIG. 6 is a composite view showing the contrast improvement of the present invention in a side-by-side comparison with conventional visual and fluorescence methods
  • FIG. 7 is a block diagram showing a sequence of image processing for generating an enhanced threshold image according to one embodiment.
  • FIG. 8 is a schematic block diagram of an imaging apparatus for caries detection according to an alternate embodiment using multiple light sources.
  • fluorescence can be used to detect dental caries using either of two characteristic responses: First, excitation by a blue light source causes healthy tooth tissue to fluoresce in the green spectrum. Secondly, excitation by a red light source can cause bacterial by-products, such as those indicating caries, to fluoresce in the red spectrum.
  • reflectance In order for an understanding of how light is used in the present invention, it is important to give more precise definition to the terms “reflectance” and “back-scattering” as they are used in biomedical applications in general and, more particularly, in the method and apparatus of the present invention.
  • reflectance generally denotes the sum total of both specular reflectance and scattered reflectance. (Specular reflection is that component of the excitation light that is reflected by the tooth surface at the same angle as the incident angle.)
  • specular component of reflectance is of no interest and is, instead, generally detrimental to obtaining an image or measurement from a sample.
  • the component of reflectance that is of interest for the present application is from back-scattered light only. Specular reflectance must be blocked or otherwise removed from the imaging path.
  • the term “back-scattered reflectance” is used in the present application to denote the component of reflectance that is of interest. “Back-scattered reflectance” is defined as that component of the excitation light that is elastically back-scattered over a wide range of angles by the illuminated tooth structure.
  • “Reflectance image” data refers to image data obtained from back-scattered reflectance only, since specular reflectance is blocked or kept to a minimum. In the scientific literature, back-scattered reflectance may also be referred to as back-reflectance or simply as back-scattering. Back-scattered reflectance is at the same wavelength as the excitation light.
  • the present invention takes advantage of the observed back-scattering behavior for incipient caries and uses this effect, in combination with fluorescence effects described previously in the background section, to provide an improved capability for dental imaging to detect caries.
  • the inventive technique hereafter referred to as fluorescence imaging with reflectance enhancement (FIRE)
  • FIRE fluorescence imaging with reflectance enhancement
  • FIRE detection can be accurate at an earlier stage of caries infection than has been exhibited using existing fluorescence approaches that measure fluorescence alone.
  • a light source 12 directs an incident light, at a blue wavelength range or other suitable wavelength range, toward tooth 20 through an optional lens 14 or other light beam conditioning component.
  • the tooth 20 may be illuminated at a proximal surface (as shown) or at an occlusal surface (not shown).
  • Two components of light are then detected by a monochrome camera 30 through a lens 22 : a back-scattered light component having the same wavelength as the incident light and having measurable reflectance; and a fluorescent light that has been excited due to the incident light.
  • specular reflection causes false positives and is undesirable.
  • the camera 30 is positioned at a suitable angle with respect to the light source 12 . This allows imaging of back-scattered light without the confounding influence of a specularly reflected component.
  • monochrome camera 30 has color filters 26 and 28 .
  • One of color filters 26 and 28 is used during reflectance imaging, the other is used during fluorescence imaging.
  • a processing apparatus 38 obtains and processes the reflectance and fluorescence image data and forms a FIRE image 60 .
  • FIRE image 60 is an enhanced diagnostic image that can be printed or can appear on a display 40 .
  • FIRE image 60 data can also be transmitted to storage or transmitted to another site for display.
  • FIG. 2 there is shown an alternate embodiment using a color camera 32 .
  • auxiliary filters would not generally be needed, since color camera 32 would be able to obtain the reflectance and fluorescence images from the color separations (also called color planes) of the full color image of tooth 20 .
  • Light source 12 is typically centered around a blue wavelength, such as about 405 nm in one embodiment. In practice, light source 12 could emit light ranging in wavelength from an upper ultraviolet range to a deeper blue, between about 300 and 500 nm.
  • Light source 12 can be a laser or could be fabricated using one or more light emitting diodes (LEDs). Alternately, a broadband source, such as a xenon lamp, having a supporting color filter for passing the desired wavelengths could be used.
  • Lens 14 or other optical element may serve to condition the incident light, such as by controlling the uniformity and size of the illumination area. For example, a diffuser 13 , shown as a dotted line in FIG. 2 , might be used before or after lens 14 to smooth out the hot spots of an LED beam.
  • the path of illumination light might include light guiding or light distributing structures such as optical fibers or a liquid light guide, for example (not shown).
  • Light level is typically a few milliwatts in intensity, but can be more or less, depending on the light conditioning and sensing components used.
  • the illumination arrangement could alternately direct light at normal incidence, turned through a beamsplitter 34 . Camera 32 would then be disposed to obtain the image light that is transmitted through beamsplitter 34 .
  • Other options for illumination include multiple light sources directed at the tooth with angular incidence from one or more sides. Alternately, the illumination might use an annular ring or an arrangement of LED sources distributed about a center such as in a circular array to provide light uniformly from multiple angles. Illumination could also be provided through an optical fiber or fiber array.
  • the imaging optics could include any suitable arrangement of optical components, with possible configurations ranging from a single lens component to a multi-element lens. Clear imaging of the tooth surface, which is not flat but can have areas that are both smoothly contoured and highly ridged, requires that imaging optics have sufficient depth of focus. Preferably, for optimal resolution, the imaging optics provide an image size that substantially fills the sensor element of the camera. Telecentric optics are advantaged for lens 22 , providing image-bearing light that is not highly dependent on ray angle.
  • Image capture can be performed by either monochrome camera 30 ( FIG. 1 ) or color camera 32 ( FIG. 2 ).
  • camera 30 or 32 employs a CMOS or CCD image sensor.
  • the monochrome version would typically employ a retractable spectral filter 26 , 28 suitable for the wavelength of interest.
  • spectral filter 26 for capturing reflectance image data would transmit predominately blue light.
  • Spectral filter 28 for capturing fluorescence image data would transmit light at a different wavelength, such as predominately green light.
  • spectral filters 26 and 28 are automatically switched into place to allow capture of both reflectance and fluorescence images in very close succession. Both images are obtained from the same position to allow accurate registration of the image data.
  • Spectral filter 28 would be optimized with a pass-band that captures fluorescence data over a range of suitable wavelengths.
  • the fluorescent effect that has been obtained from tooth 20 can have a relative broad spectral distribution in the visible range, with light emitted that is outside the wavelength range of the light used for excitation.
  • the fluorescent emission is typically between about 450 nm and 650 nm, while generally peaking in the green region, roughly from around 500 nm to about 600 nm.
  • a green light filter is generally preferred for spectral filter 28 in order to obtain this fluorescence image at its highest energy levels.
  • other ranges of the visible spectrum could also be used in other embodiments.
  • spectral filter 26 would be optimized with a pass-band that captures reflectance data over a wavelength range covering at least a significant portion of the spectral energy of the light source 12 used.
  • a blue light filter is generally used for spectral filter 26 in order to obtain the reflectance image at its highest energy level.
  • Camera controls are suitably adjusted for obtaining each type of image. For example, when capturing the fluorescence image, it is necessary to make appropriate exposure adjustments for gain, shutter speed, and aperture, since this image may not be intense.
  • color camera 32 FIG. 2
  • color filtering is performed by the color filter arrays on the camera image sensor. The reflectance image is captured in the blue color plane; simultaneously, the fluorescence image is captured in the green color plane. That is, a single exposure captures both back-scattered reflectance and fluorescence images.
  • Processing apparatus 38 is typically a computer workstation but may, in its broadest application, be any type of control logic processing component or system that is capable of obtaining image data from camera 30 or 32 and executing image processing algorithms upon that data to generate the FIRE image 60 data. Processing apparatus 38 may be local or may connect to image sensing components over a networked interface.
  • FIG. 5 there is shown, in schematic form, how the FIRE image 60 is formed according to the present invention.
  • Two images of tooth 20 are obtained, a green fluorescence image 50 and a blue reflectance image 52 .
  • the reflectance light used for reflectance image 52 and its data is from back-scattered reflectance, with specular reflectance blocked or kept as low as possible.
  • there is a carious region 58 represented in phantom outline in each of images 50 , 52 , and 60 , that causes a slight decrease in fluorescence and a slight increase in reflectance.
  • the carious region 58 may be imperceptible or barely perceptible in either fluorescence image 50 or reflectance image 52 , taken individually.
  • Processing apparatus 38 operates upon the image data using an image processing algorithm as discussed below for both images 50 and 52 and provides FIRE image 60 as a result.
  • the contrast between carious region 58 and sound tooth structure is heightened, so that a caries condition is made more visible in FIRE image 60 .
  • FIG. 6 shows the contrast improvement of the present invention in a side-by-side comparison with a visual white-light image 54 and conventional fluorescence methods.
  • the carious region 58 may look indistinct from the surrounding healthy tooth structure in white-light image 54 , either as perceived directly by eye or as captured by an intraoral camera.
  • the carious region 58 may show up as a very faint, hardly noticeable shadow.
  • the FIRE image 60 generated by the present invention, the same carious region 58 shows up as a darker, more detectable spot.
  • the FIRE image 60 offers greater diagnostic value.
  • processing of the image data uses both the reflectance and fluorescence image data to generate a final image that can be used to identify carious areas of the tooth.
  • this image processing performs the following operation for each pixel: (m*F value ) ⁇ (n*R value ) (1) where m and n are suitable multipliers (positive coefficients) and F value and R value are the code values obtained from fluorescence and reflectance image data, respectively.
  • Back-scattered reflectance is higher (brighter) for image pixels in the carious region, yielding a higher reflectance value R value for these pixels than for surrounding pixels.
  • the fluorescence meanwhile, is lower (darker) for image pixels in the carious region, yielding a lower fluorescence value F value for these pixels than for surrounding pixels.
  • the fluorescence is considerably weaker in intensity compared to the reflectance.
  • scalar multiplier n for reflectance value R value is one.
  • a thresholding operation executed using image processing techniques familiar to those skilled in the imaging arts, or some other suitable conditioning of the combined image data used for FIRE image 60 , may be used to further enhance the contrast between a carious region and sound tooth structure.
  • FIG. 7 there is shown, in block diagram form, a sequence of image processing for generating an enhanced threshold FIRE image 64 according to one embodiment. Fluorescence image 50 and reflectance image 52 are first combined to form FIRE image 60 , as described previously. A thresholding operation is next performed, providing threshold image 62 that defines more clearly the area of interest, carious region 58 .
  • threshold image 62 is combined with original FIRE image 60 to generate enhanced threshold FIRE image 64 .
  • results of threshold detection can also be superimposed onto a white light image 54 ( FIG. 6 ) in order to definitively outline the location of a carious infection.
  • m and n are dependent on the spectral content of the light source and the spectral response of the image capture system. There is variability in the center wavelength and spectral bandwidth from one LED to the next, for example. Similarly, variability exits in the spectral responses of the color filters and image sensors of different image capture systems. Such variations affect the relative magnitudes of the measured reflectance and fluorescence values. Therefore, it may be necessary to determine a different m and n value for each imaging apparatus 10 as a part of an initial calibration process. A calibration procedure used during the manufacturing of imaging apparatus 10 can then optimize the m and n values to provide the best possible contrast enhancement in the FIRE image that is formed.
  • a spectral measurement of the light source 12 used for reflectance imaging is obtained. Then, spectral measurement is made of the fluorescent emission that is excited from the tooth. This data provides a profile of the relative amount of light energy available over each wavelength range of interest. Then the spectral response of camera 30 (with appropriate filters) or 32 is quantified against a known reference. These data are then used, for example, to generate a set of optimized multiplier m and n values to be used by processing apparatus 38 of the particular imaging apparatus 10 for forming FIRE image 60 .
  • any number of more complex image processing algorithms could alternately be used for combining the reflectance and fluorescence image data in order to obtain an enhanced image that identifies carious regions more clearly. It may be advantageous to apply a number of different imaging algorithms to the image data in order to obtain the most useful result.
  • an operator can elect to use any of a set of different image processing algorithms for conditioning the fluorescence and reflectance image data obtained. This would allow the operator to check the image data when processed in a number of different ways and may be helpful for optimizing the detection of carious lesions having different shape-related characteristics or that occur over different areas of the tooth surface.
  • the image contrast enhancement achieved in the present invention is advantaged over conventional methods that use fluorescent image data only.
  • image processing has been employed to optimize the data, such as to transform fluorescence data based on spectral response of the camera or of camera filters or other suitable characteristics.
  • the method of the '2356 Stookey et al. disclosure, cited above performs this type of optimization, transforming fluorescence image data based on camera response.
  • these conventional approaches overlook the added advantage of additional image information that the back-scattered reflectance data obtains.
  • the contrast of either or both of the reflectance and fluorescence images may be improved by the use of a polarizing element.
  • enamel having a highly structured composition, is sensitive to the polarization of incident light.
  • Polarized light has been used to improve the sensitivity of dental imaging techniques, for example, in “Imaging Caries Lesions and Lesion Progression with Polarization Sensitive Optical Coherence Tomography” in J. Biomed Opt ., October 2002; 7(4): pp. 618-27, by Fried et al.
  • Polarization control can also be advantageously employed as a means to minimize specular reflection.
  • Specular reflection tends to preserve the polarization state of the incident light.
  • the specular reflected light is also S-polarized.
  • Back-scattering tends to de-polarize or randomize the polarization of the incident light.
  • incident light is S-polarized
  • back-scattered light has both S- and P-polarization components. Using a polarizer and analyzer, this difference in polarization handling can be employed to help eliminate unwanted specular reflectance from the reflectance image, so that only back-scattered reflectance is obtained.
  • FIG. 4A there is shown an embodiment of imaging apparatus 10 that employs a polarizer 42 in the path of illumination light.
  • Polarizer 42 passes linearly polarized incident light.
  • An analyzer 44 may be provided in the path of image-bearing light from tooth 20 as a means to minimize specular reflection component.
  • reflectance light sensed by camera 30 or 32 is predominantly back-scattered light, that portion of the reflectance that is desirable for combination with the fluorescence image data according to the present invention.
  • polarizer 42 In the case where the illumination light from light source 12 is already linearly polarized, such as from a laser, polarizer 42 is not needed; analyzer 44 would then be oriented with its polarization axis orthogonal to the polarization direction of the illumination light for rejecting specular reflection.
  • FIG. 4B An alternate embodiment, shown in FIG. 4B , employs a polarizing beamsplitter 18 (sometimes termed a polarization beamsplitter) as a polarizing element.
  • polarizing beamsplitter 18 advantageously performs the functions of both the polarizer and the analyzer for image-bearing light, thus offering a more compact solution. Tracing the path of illumination and image-bearing light shows how polarizing beamsplitter 18 performs this function.
  • Polarization beamsplitter 18 transmits P-polarization, as shown by the dotted arrow in FIG. 4B , and reflects S-polarization, directing this light to tooth 20 . Back-scattering by the tooth 20 structure depolarizes this light.
  • Polarization beamsplitter 18 treats the back-scattered light in the same manner, transmitting the P-polarization and reflecting the S-polarization. The resulting P-polarized light can then be detected at camera 30 (with suitable filter as was described with reference to FIG. 1 ) or color camera 32 . Because specularly reflected light is S-polarized, polarization beamsplitter 18 effectively removes this specular reflective component from the light that reaches camera 30 , 32 .
  • Polarized illumination results in further improvement in image contrast, but at the expense of light level, as can be seen from the description of FIGS. 4A and 4B .
  • polarizer 42 One type of polarizer 42 that has particular advantages for use in the present application is the wire grid polarizer, such as those available from Moxtek Inc. of Orem, Utah and described in U.S. Pat. No. 6,122,103 (Perkins et al.)
  • the wire grid polarizer exhibits good angular and color response, with relatively good transmission over the blue spectral range.
  • Either or both polarizer 42 and analyzer 44 in the configuration of FIG. 4A could be wire grid polarizers.
  • Wire grid polarizing beamsplitters are also available, and can be used in the configuration of FIG. 4B .
  • the method of the present invention takes advantage of the way the tooth tissue responds to incident light of sufficient intensity, using the combination of fluorescence and light reflectance to indicate carious areas of the tooth with improved accuracy and clarity.
  • the present invention offers an improvement upon existing non-invasive fluorescence detection techniques for caries.
  • images that have been obtained using fluorescence only may not clearly show caries due to low contrast.
  • the method of the present invention provides images having improved contrast and is, therefore, of more potential benefit to the diagnostician for identifying caries.
  • the method of the present invention also provides images that can be used to detect caries in its very early incipient stages. This added capability, made possible because of the perceptible back-scattering effects for very early carious lesions, extends the usefulness of the fluorescence technique and helps in detecting caries during its reversible stages, so that fillings or other restorative strategies might not be needed.
  • light sources 12 could be used, with various different embodiments employing a camera or other type of image sensor. While a single light source 12 could be used for fluorescence excitation, it may be beneficial to apply light from multiple incident light sources 12 for obtaining multiple images.
  • light source 12 might be a more complex assembly that includes one light source 16 a for providing light of appropriate energy level and wavelength for exciting fluorescent emission and another light source 16 b for providing illumination at different times.
  • the additional light source 16 b could provide light at wavelength and energy levels best suited for back-scattered reflectance imaging.
  • white light illumination or other polychromatic illumination
  • the white light image itself might also provide the back-scattered reflectance data that is used with the fluorescence data for generating the FIRE image.
  • Supporting optics for both illumination and image-bearing light paths could have any number of forms.
  • a variety of support components could be fitted about the tooth and used by the dentist or dental technician who obtains the images. Such components might be used, for example, to appropriately position the light source or sensing elements or to ease patient discomfort during imaging.

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US11/262,869 2005-10-31 2005-10-31 Method and apparatus for detection of caries Active 2027-06-30 US7596253B2 (en)

Priority Applications (8)

Application Number Priority Date Filing Date Title
US11/262,869 US7596253B2 (en) 2005-10-31 2005-10-31 Method and apparatus for detection of caries
EP06826069A EP1942794A2 (en) 2005-10-31 2006-10-16 Method and apparatus for detection of caries
PCT/US2006/040472 WO2007053293A2 (en) 2005-10-31 2006-10-16 Method and apparatus for detection of caries
JP2008537765A JP5441411B2 (ja) 2005-10-31 2006-10-16 う蝕検知の方法
US12/541,329 US7974453B2 (en) 2005-10-31 2009-08-14 Method and apparatus for detection of caries
US13/117,759 US8396272B2 (en) 2005-10-31 2011-05-27 Method and apparatus for detection of caries
US13/117,724 US8345942B2 (en) 2005-10-31 2011-05-27 Method and apparatus for detection of caries
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